Blood pressure monitoring system and method having an extended optical range

ABSTRACT

A system and method for monitoring blood pressure of a wearer has an inflatable arm cuff that is selectably inflatable to differing air pressures that incorporates a fabric having both a light transmission property and a light reflection property when the fabric is illuminated with light having wavelength(s) in the range from about 400 to about 2200 nanometers. A radiation source and a detector are attached to the fabric in relative positions such that the reception of incident radiation by the detector is directly affected by a change in the amount of light transmitted through the fabric relative to the amount of light reflected by the fabric as the fabric stretches in response to motion in the body of a wearer due to changes in the flow of blood through an artery disposed beneath the fabric occurring in consonance with variations in the air pressure within the inflatable cuff.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a divisional of U.S. Ser. No. 12/054,608, filed Mar. 25, 2008, currently pending, which was a divisional U.S. Ser. No. 10/937,121, filed Sep. 9, 2004, issued as U.S. Pat. No. 7,381,187 on Jun. 3, 2008.

Subject matter disclosed herein is disclosed in the following co-pending provisional applications filed Sep. 12, 2003, from which priority is claimed:

System for Monitoring Motion of a Member, U.S. Application No. 60/502,760; filed in the name of Chia Kuo and George W. Coulston;

Blood Pressure Monitoring System and Method, U.S. Application No. 60/502,751; filed in the names of George W. Coulston and Thomas A. Micka; and

Reflective System for Monitoring Motion of a Member, U.S. Application No. 60/502,750; filed in the name of George W. Coulston.

Subject matter disclosed herein is disclosed in the following co-pending provisional applications filed Dec. 2, 2003, from which priority is claimed: Blood Pressure Monitoring System and Method Having Extended Optical Range, U.S. Application No. 60/526,187; filed in the names of George W. Coulston and Thomas A. Micka;

Extended Optical Range Reflective System for Monitoring Motion of a Member, U.S. Application No. 60/526,429; filed in the name of George W. Coulston; and

Extended Optical Range System for Monitoring Motion of a Member, U.S. Application No. 60/526,188; filed in the name of Chia Kuo and George W. Coulston.

BACKGROUND OF THE INVENTION

1. Field of the Invention

This invention relates to a system and a method for monitoring blood pressure which utilizes a fabric having predetermined optical properties that respond to the motion generated by geometric changes in the body due to the conduction of blood through an artery located beneath the fabric.

2. Description of the Prior Art

The “pulse” of the heart is associated with pressure pulses known to exist in the arteries carrying blood throughout the body. The periodic pumping of the heart produces these pressure pulses which in turn flex the artery walls in rhythm with the pumping of the heart. The maximum, or peak, pressure exerted against the arterial wall occurs during the systole phase of the beat and is termed “systolic pressure”. The lowest, or baseline, pressure (known as the “diastolic pressure”) occurs during the diastole phase of the beat.

As the heart beats the pressure in the arteries fluctuates (higher during the systole phase and lower during the diastole phase of the beat) and is best described by the values for the systolic and diastolic pressures. Typical practice is to express blood pressure as a ratio of the maximum and minimum values.

The generally known method to determine these two blood pressure extremes is the auscultatory method. In this method a pressure cuff is applied to the upper arm of a person. This cuff includes a bladder capable of holding air at a predetermined known pressure. The cuff bladder is inflated to a pressure above the highest expected pressure to be measured, i.e. above the systolic pressure. Inflated at this highest pressure the cuff prevents the flow of blood in the brachial artery of the arm underlying the pressure cuff. The bladder is equipped with a valve, which allows the pressure to be reduced in a controlled way.

As air is released from the bladder, blood flow in the brachial artery is re-established. The inflow of blood through the artery is accompanied by pulsing sounds known as the Korotkoff sounds. These sounds are detected using a stethoscope at a point on the brachial artery just below the pressure cuff. The falling pressure in the cuff bladder is observed while air is released.

The Korotkoff sounds are divided in five phases based on loudness and certain qualitative features. The five phases of the Korotkoff sounds are also identified with certain pressure regimes, as normal arterial blood flow is being re-established. The first phase of the Korotkoff sounds (Phase 1) is heard at about 120 millimeters of mercury (mm Hg) characterized by a sharp “thud”; this is the systolic (maximum) blood pressure. Phase 2 is identified with a pressure of about 110 mm Hg and is heard as a swishing or blowing sound. Phase 3 is identified with a pressure of about 100 mm Hg and is described as a thud which is softer than that of Phase 1. At a pressure of about 90 mm Hg the first diastolic pressure is detected, called the Phase 4 Korotkoff sound, and heard as a softer blowing sound which disappears. Phase 5 is identified with about 80 mm Hg and is called the second diastolic pressure. This last phase is silent, meaning that a laminar blood flow has been again established. Phase 5 may be absent in some human subjects. For this reason, the first diastolic pressure of Phase 4 is recorded as the lowest pressure in the artery.

An automated auscultatory apparatus relies on detecting sound levels and complex processing of these sounds into electronic signals, which are correlated, with the phases of the Korotkoff sounds. Representative of an automated arrangement that uses auscultatory method is that measurement system disclosed in U.S. Pat. No. 6,511,435 (Bluth et al.)

The re-establishment of blood flow in an occluded artery is also accompanied by a relatively significant flexure of the arterial wall. The flexure diminishes as the artery widens with the decrease in cuff pressure. In an alternative form of blood pressure measuring apparatus, known as an oscillatory measurement system, the mechanical vibrations accompanying arterial wall flexure are transformed into sound as they enter the inflated bladder of the cuff. This sound is detectable using a microphone located in the bladder.

One drawback of the oscillatory measuring apparatus is its reliance upon a cuff bladder modified to contain a microphone and associated connections to an external signal processor. The reliance on a microphone to detect changes in sound pressure level and pattern recognition from the waveform so generated is difficult.

An oscillatory blood pressure measurement arrangement is also disclosed in the above-mentioned U.S. Pat. No. 6,511,435 (Bluth et al.). U.S. Pat. No. 6,458,085 (Wu et al.) discloses oscillatory blood pressure measurement arrangement.

SUMMARY OF THE INVENTION

The present invention is directed to a system and method for monitoring blood pressure by detecting motion due to geometric changes in the body of a subject.

The present invention is usable with an inflatable arm cuff that is selectably inflatable to differing air pressures and is characterized by a patch at least a portion of which is formed from a fabric which has both a light transmission property and a light reflection property when the fabric is illuminated with light in the range from 400 nanometers to 2200 nanometers and particularly in the ranges from about 400 to 800 nanometers and from about 700 to 2200 nanometers. The amount of light transmitted through the fabric relative to the amount of light reflected by the fabric is able to change when the fabric stretches in response to motion in the body of a wearer due to changes in the flow of blood through an artery disposed beneath the patch. A source of radiation in the range from 400 nanometers to 2200 nanometers and particularly in the ranges from about 400 to 800 nanometers and from about 700 to 2200 nanometers and a detector are attached to the fabric in relative positions such that the reception of incident radiation by the detector is directly affected by a change in the amount of light transmitted through the fabric relative to the amount of light reflected by the fabric as the fabric stretches in response to motion in the body of a wearer due to changes in the flow of blood through an artery disposed beneath the patch occurring in consonance with variations in the air pressure within the inflatable cuff. A pressure recorder responsive to the signal output from the detector records the pressure of the cuff when the output of the detector is at a minimum value and the pressure in the cuff following the minimum when the signal from the detector again lies within a predetermined range of a baseline signal value.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will be more fully understood from the following detailed description, taken in connection with the accompanying drawing, which forms a part of this application, and in which:

FIG. 1 is a schematic diagram of a system useful for the monitoring blood pressure of the subject by sensing geometric changes in the body of the subject due to the motion of blood passing through blood vessels underlying a patch of monitoring fabric;

FIGS. 2A and 2B are respective diagrammatic views illustrating the response of the fabric used in the monitoring system of the present invention during normal systole and diastole phases of heart action;

FIGS. 2C and 2D are respective diagrammatic views illustrating the response of the monitoring fabric when a blood vessel underlying a patch of monitoring fabric is totally occluded and when blood flow is re-established;

FIG. 2E is a graphical representation of the change in the amount of light transmitted through the monitoring fabric relative to the amount of light reflected by the monitoring fabric as the fabric stretches (i.e., elongates and recovers) during normal systole and diastole phases of heart action (FIGS. 2A and 2B) and when a blood vessel underlying a patch of monitoring fabric is totally occluded and when blood flow is thereafter re-established (FIGS. 2C and 2D);

FIG. 2F is a graphical representation of a signal, periodic in time, representing the changes in the amount of light transmitted through the monitoring fabric relative to the amount of light reflected by the monitoring fabric as represented in FIG. 2E; and

FIG. 3 is a diagram illustrating the temporal relationship between pressure measured in an inflatable cuff disposed over an artery of a wearer and the voltage appearing of the detector when the method and system of the present invention is used to monitor blood pressure of the wearer.

DETAILED DESCRIPTION OF THE INVENTION

Throughout the following detailed description similar reference characters refer to similar elements in all figures of the drawings.

FIG. 1 is a stylized pictorial representation of a system 10 useful with the method of the present invention for directly monitoring blood pressure of a subject by sensing motion due to geometric changes in the body of the subject associated with the flexing of arterial walls produced by blood pressure pulses.

As seen in FIG. 1, the system 10 includes a sleeve 12 having any convenient fabric construction (e.g., knitting, weaving) and made from any suitable textile filament apparel denier yarn. The sleeve 12 includes at least a portion, or patch 14, formed from a monitoring fabric 16. The monitoring fabric 16 has an interior surface 161 and exterior surface 16E. Although the patch 14 is represented as rectangular in shape in FIG. 1 it should be understood that the patch 14 may take any convenient or desired shape. If desired the entirety of the sleeve 12 may be made from the monitoring fabric 16.

The monitoring fabric 16 in accordance with the present invention exhibits both a light transmission property and a light reflection property when the fabric is illuminated with light having a wavelength in the extended range from about 400 to about 2200 nanometers. This range is extended in the sense that it encompasses both near infrared light and visible broad spectrum white light.

As used herein the term “broad spectrum white light” means light having a wavelength in the range from about four hundred-(400) nanometers to about eight hundred (800) nanometers.

As used herein the term “near infrared light” means light having a wavelength in the range from about seven hundred (700) nanometers to about twenty two hundred (2200) nanometers. For use in systems operating in the near infrared regime and embodying the teachings of the present invention particularly the wavelength of 805 nanometers or the wavelength of 880 nanometers may be used. The wavelength of 805 nanometers is preferred.

In accordance with the present invention, the amount of light transmitted through the fabric 16 relative to the amount of light reflected by the fabric 16 is able to change as the fabric stretches. The fabric stretches in response to geometric changes of the body of the subject due to the flexing of the arteries in response to blood pressure pulses. The term “light balance” may be used herein to refer to the amount of light transmitted through the fabric 16 relative to the amount of light reflected by the fabric 16.

Light reflected by the fabric toward an aperture of acceptance defined with respect to an axis extending from the surface of the fabric is useful in producing a signal output from a detector located in the aperture. Alternatively, light transmitted through the fabric is “lost” to a detector placed at the aperture of acceptance.

The monitoring fabric 16 used in the patch 14 is made as a combination of reflective yarns and stretchable yarns. The yarns can be combined in any conventional manner including woven or non-woven construction. In a suitable construction a first plurality of reflective yarns is woven or knitted with a second plurality of stretchable yarns. Each reflective yarn has a coating of a specularly reflective material thereon. The coating may also be electrically conductive. Each stretchable yarn is formed as a combination of a covered spandex yarn and a hard yarn.

In the preferred instance the reflective yarn is that yarn sold by Laird Sauquoit Technologies, Inc. (300 Palm Street, Scranton, Pa., 18505) under the trademark X-STATIC® yarn. X-STATIC® yarn is based upon a 70 denier (77 dtex), 34 filament textured nylon available from INVISTA North America S. à r. l., Wilmington, Del. 19805, as product ID 70-XS-34×2 TEX 5Z electroplated with electrically conductive silver.

In one preferred embodiment, the covered elastic yarn can be comprised of a twenty (20) denier (22 dtex) LYCRA® spandex yarn single-covered with a ten (10) denier (11 dtex) seven filament nylon yarn. LYCRA® spandex yarn is available from INVISTA North America S. à r. l., Wilmington, Del. 19805. Alternatively, the elastic yarn component of the present invention may comprise elastane yarn or polyester bicomponent yarns such as those known as ELASTERELL-P™ from INVISTA™ S. à r. I. North America Inc. of Wilmington, Del. The terms spandex and elastane are used interchangeably in the art. An example of a branded spandex yarn suitable for use with the present invention is LYCRA®.

Each stretchable yarn is formed as a combination of a covered elastic yarn component and a hard yarn component. Preferably the covered elastic yarn component is comprised of a twenty (20) denier (22 dtex) LYCRA® spandex yarn single-covered with a ten (10) denier (11 dtex) seven filament nylon yarn. LYCRA® spandex yarn is available from INVISTA North America S. à r. l., Wilmington, Del. 19805. The hard component comprises a 260 denier (286 dtex) 68 filament nylon yarn.

Synthetic bicomponent multifilament textile yarns may also be used to form the elastic yarn component. One preferred synthetic bicomponent filament component polymer can be thermoplastic. The synthetic bicomponent filaments can be melt spun or formed in any other manner common in the art of filament formation. In the most preferred embodiment the component polymers can be polyamides or polyesters.

A preferred class of polyamide bicomponent multifilament textile yarns comprises those nylon bicomponent yarns which are self-crimping, also called “self-texturing”. These bicomponent yarns comprise a component of nylon 66 polymer or copolyamide having a first relative viscosity and a component of nylon 66 polymer or copolyamide having a second relative viscosity, wherein both components of polymer or copolyamide are in a side-by-side relationship as viewed in the cross section of the individual filament. Self-crimping nylon yarn such as that yarn sold by DuPont Textiles and Interiors under the trademark TACTEL® T-800™ is an especially useful bicomponent elastic yarn.

Some examples of polyester component polymers include polyethylene terephthalate (PET), polytrimethylene terephthalate (PTT) and polytetrabutylene terephthalate. In one preferred embodiment polyester bicomponent filaments comprise a component of PET polymer and a component of PTT polymer in a side-by-side relationship as viewed in the cross section of the individual filament. One exemplary yarn having this structure is sold by DuPont Textiles and Interiors under the trademark T-400™ Next Generation Fiber.

The hard component could be made from any inelastic synthetic polymer fiber(s) or from natural textile fibers such as wool, cotton, ramie, linen, rayon, silk, and the like. The synthetic polymer fibers may be continuous filament or staple yarns selected from multifilament flat yarns, partially oriented yarns, textured yarns, bicomponent yarns selected from nylon, polyester or filament yarn blends. The hard component is preferably 260 denier (286 dtex) 68 filament nylon yarn.

Nylon yarns may comprise synthetic polyamide component polymers such as nylon 6, nylon 66, nylon 46, nylon 7, nylon 9, nylon 10, nylon 11, nylon 610, nylon 612, nylon 12 and mixtures and copolyamides thereof are preferred. In the case of copolyamides, especially preferred are those including nylon 66 with up to 40 mole percent of a polyadipamide wherein the aliphatic diamine component is selected from the group of diamines available from E, I. Du Pont de Nemours and Company, Inc. (Wilmington, Del., USA, 19880) under the respective trademarks DYTEK A® and DYTEK EP®

Further in accordance with the present invention, the hard yarn portion of the present invention may comprise polyesters such as, for example, polyethylene terephthalate, polytrimethylene terephthalate, polybutylene terephthalate and copolyesters thereof.

The monitoring fabric 16 used in the patch 14 can be made according to any conventional textile means including warp knitting, weft knitting, weaving, braiding, or through non-woven construction. The monitoring fabric 16 may also be formed from composite yarns in which the reflective and stretchable components are combined in the same yarn. Such a composite yarn would include a covering yarn having a spectrally reflective outer surface that is wrapped about an elastic yarn component in one or more layers.

The remainder of the structure of the sleeve 12 may exhibit any convenient textile construction (e.g., knitting, weaving) and may be made from any suitable textile filament apparel denier yarn.

In one embodiment, the monitoring fabric 16 used in the patch 14 is attached to the sleeve 12. The patch 14 could be sewn, glued, taped, buttoned, interwoven or attached to the garment by any conventional means. In another embodiment, the sleeve 12 completely constructed of the monitoring fabric 16.

The present invention is directed to monitoring the light balance of a monitoring fabric 16 as it stretches and recovers. For this purpose the system 10 includes a suitable source 18 of radiation operable in the wavelength range from 400 nanometers to 2200 nanometers, and particularly in the wavelength ranges from about 400 to 800 nanometers and from about 700 to 2200 nanometers. An associated detector 22 is responsive to incident radiation in the given wavelength range and sub-ranges for producing signals in response thereto.

The source 18 of radiation is attached to the surface 16E of the monitoring fabric 16. The detector 22 is also attached to the surface 16E. Electrical connections 24 connect the source 18 and the detector 22 with a signal processor 26. The processor 26 may conveniently include a source of electric energy to operate both the source 18 and the detector 22.

The source is arranged in such a way as to maintain its relative position to the detector. For instance, the source 18 and detector 22 may be rigidly connected together on one side of the fabric to maintain a spatial relationship. Alternatively, the position of the source 18 relative to the detector 22 can be maintained on opposite sides of the monitoring fabric 16 for monitoring transmission. In such an embodiment, the radiation source is connected to the radiation detector using a “clothes-pin” or alligator style clamp. Other well known means of maintaining the spatial relationship of the source relative to the detector are contemplated.

In the case of operation with near infrared light, the radiation source 18 can be a compound semiconductor-based (e.g., gallium arsenide or gallium aluminum arsenide) photo-emitting diode operating in the infrared range (at a wavelength of 805 nanometers or 880 nanometers) or any similar radiation source. The radiation detector 22 can be any device that can detect radiation, for instance, a photodiode coupled to appropriately configured output amplification stages. Any well known semiconductors can be used for forming the photodiode including silicon or germanium. A commercially available radiation source and detector package suitable for use in the system of the present invention is that available from Fourier Systems Ltd. (9635 Huntcliff Trace, Atlanta, Ga., 30350) as model DT155 (0-5 volt output).

For broad spectrum white light (400 to 800 nanometers) operation, the source 18 can be a compound semiconductor-based “white LED” (e.g., a light emitting diode employing an indium gallium nitride based device with suitable phosphors to provide broad spectrum white light emission). The detector 22 is preferably a silicon phototransistor coupled to appropriately configured output amplification stages.

The radiation source 18 and the detector 22 are attached to monitoring fabric 16 in predetermined relative positions. The positions were determined such that the reception of incident radiation by the detector 22 is directly affected by a change in the amount of light transmitted through the monitoring fabric 16 relative to the amount of light reflected by the monitoring fabric 16 when the fabric stretches and recovers. In the preferred case the radiation source 18 and detector 22 are embedded, or fixed firmly, into the textile structure of the monitoring fabric 16. The radiation source 18 and detector 22 can be fixed using any well known attachment method, including but not limited to, clamping, gluing, sewing, taping, or Velcro-attachment. Optionally, it may be desirable in some operational configurations of the invention to dispose both the source and the detector remote from and not in direct contact with the fabric 16. In such a remote arrangement, the radiation source 18 and detector 22 could be located in any arrangement that permits the detector 22 to detect changes in the transmission and reflection of radiation during stretching and recovery.

The apparatus 10 represented in FIG. 1 further includes an inflatable cuff 28 substantially similar to a standard cuff known in the blood pressure measurement art. The cuff 28 is typically a woven nylon sleeve with a seamless inner bladder 30 of latex rubber. The inner bladder 30 communicates with an external air pump 32, valve 34 and a pressure measurement device 36 for measuring the internal pressure of the bladder 30. The pressure measurement device 36 communicates electrically with the processor 26 over an electrical connection 38. The valve 34 may be configured for automatic operation by the signal processor 26 over a control line 40.

The pump 32 may take the form of any conventional pump including a manually operated device, an automated piston or diaphragm air pump. The pressure measurement device 36 may be implemented using a manometer of any known design. Such a manometer is constructed using known barometric measurement techniques that include a column of mercury, a Bourdon gauge movement, and a measurement device having a high reproducibility of measurement in the expected range of operation, for example, from about ten (10) millimeters of mercury to about five hundred (500) millimeters of mercury (mm Hg). A suitable pressure measurement device 36 could be a direct capacitance measurement device provided with a fully electronic output suitable for use with traditional digital signal processors. A pressure transducer operable to measure the pressure within the cuff at predetermined sampling time intervals is also suitable for use as the pressure measurement device. The miniature silicon pressure sensor package available from Advanced Custom Sensors, Inc. Irvine, Calif., 92618 as Model 7277 (zero to five volt output; zero to seven pounds per square inch gage rating) is such a device, though any similar means for measuring pressure is contemplated.

The principles of operation by which the motion of a subject's body due to geometric changes generated by blood pressure pulses may be monitored in accordance with the system of the present invention may be more clearly understood with reference to FIGS. 2A through 2F. In the discussion that follows both the source 18 and the detector 22 are mounted adjacent to the same surface 16E of the monitoring fabric 16 so as to operate in a reflection mode. Alternatively, it is contemplated within the scope of the invention to operate in a transmission mode. In the alternative transmission mode of operation, the source 18 and the detector 22 are mounted adjacent to the same surface 161 of the monitoring fabric 16.

The reaction of the fabric 16 during normal diastole and systole phases of heart action are depicted in FIGS. 2A and 2B.

As represented in FIG. 2A in a normal diastole phase the yarns 16Y forming the monitoring fabric 16 lie within a relatively close distance of each other to define a pattern of relatively narrow gaps 16G. A generally circular spot indicated by the reference character 17 represents the area of the monitoring fabric 16 illuminated by the source 18. Of the photons emitted from the source 18 toward the surface 16E of the fabric 16 some photons are absorbed (e.g., represented by a ray 18C) by the yarns 16Y of the fabric while other photons (e.g., the rays 18A and 18B) pass through gaps 16G therein. These photons are lost to the detector 22. The major portion of the light (e.g., represented by the rays 18D through 18G) is reflected from the surface 16E of the monitoring fabric 16 toward the detector 22 and is useful in producing a corresponding output signal therefrom.

During a normal systole phase of a heart beat the size of the gaps 16G formed in the monitoring fabric 16 increase in response to motion induced by the flexure of the underlying blood vessels. This increase in size of the gaps 16G increases the likelihood that a photon will pass through the fabric 16 and decreases the likelihood that a photon will reflect toward the detector 22. The total number of photons lost to the detector 22 by transmission or absorption through the fabric (e.g., represented by the rays 18A, 18B and 18C) increases. The signal output from the detector 22 in reflection mode concomitantly decreases. Although the number of photons lost to the detector 22 by absorption (e.g., represented by the ray 18C) does not necessarily change, the likelihood that a photon will strike a yarn 16F and be reflected or absorbed decreases since the spot size 17 remains constant in area while the gap 16G size increases.

As the systolic phase of the pulse beat gives way to the diastolic phase the fabric 16 undergoes elastic recovery. The gaps 16G return to their original size (FIG. 2A). The major portion of the light is again reflected toward the detector 22, increasing the output signal therefrom.

The left hand portion of FIG. 2E illustrates the waveform of the signal generated at the detector 22 as the fabric undergoes its stretch cycle from the initial diastolic phase (represented by the reference character “I”) through a systolic phase (represented by the reference character “II”) and back to the diastolic phase (“I”). This portion of FIG. 2E graphically illustrates that during the course of a stretch cycle the light balance (reference character “LB” in FIG. 2E) of the fabric changes.

Comparison of the diastolic and systolic phases indicates that the amount of light transmitted through the monitoring fabric 16 relative to the amount of light reflected by the monitoring fabric 16 changes in a periodic fashion over time as the fabric stretches. Light lost to the detector 22 by absorption may be considered as contributing to the “transmitted light” section of the graph. This periodic variation in light balance is represented in the left-hand portion of FIG. 2F as a time-varying signal synchronized with the elongation and recovery stages of fabric stretch.

The situation that arises when a cuff is fully pressurized is depicted in FIG. 2C. In this case the flow of blood is completely interrupted and no flexure of the underlying artery occurs. The fabric 16 reverts to a fully unstretched condition with the gap spacing 16G between yarns 16Y being at its minimum. Substantially all of the photons falling on the illuminated spot 17 are reflected toward the detector 22 resulting in the light balance depicted at reference character “III” in the right hand portion of FIG. 2E.

FIG. 2D depicts the situation when blood flow through the previously occluded artery is re-established. The sudden rush of blood through the artery elongates the fabric 16 and extends the gaps 16G to their widest extent. The amount of light transmitted through the fabric increases commensurately while the amount of light reflected significantly decreases. This result is illustrated in the light balance depicted at reference character “IV” in the right hand portion of FIG. 2E. The right hand portion of FIG. 2F illustrates the rapid decrease in signal output from the detector 22 caused by the sudden rush of blood through the previously occluded artery.

As the rush of blood diminishes the light balance and the signal output from the detector would revert toward the ranges exhibited during normal diastolic and systolic operation.

OPERATION

In an exemplary mode of operation the apparatus of the present invention would be applied to the arm of a person generally in the position indicated by the dotted outline in FIG. 1 using care to place the fabric patch 16 of sleeve 12 over the brachial artery. The inflatable cuff 30 is applied over the sleeve 12.

FIG. 3 illustrates the temporal relationship between pressure measured in the cuff 30 and a voltage resulting from the radiation detected by the detector 22 in reflection mode. In a reflection mode of operation the source 18 and the detector 22 are arranged adjacent to side 16E of the fabric 16. As discussed in connection with FIGS. 2A through 2F any fabric 16 elongation is accompanied by a decreasing signal (voltage) from the detector 22, corresponding to increased light transmission through the fabric 16.

Considering again FIG. 3, the pressure in the cuff 30 is equal to atmospheric pressure P₀ during the time interval between t₀ and t₁. Also, during this same time interval the signal at detector 22 is a mean value V_(N) varying between the limits of (V_(N)+Δ and (V_(N)−Δ)

This mean voltage V_(N) results from the subtle flexing of the arterial walls and subsequent subtle movement of tissue underlying the fabric 16. This subtle movement is due to the arterial pressure fluctuations from the systolic to the diastolic pressure extremes. Because blood flow is laminar and silent during this interval the net average force on the arterial walls is constant. During the arbitrary time interval t_(o) to t₁ the voltage reading from detector 22 is sampled; a voltage V_(N) (+/−Δ) is stored in memory of the processor 26.

Next, at time t₁, under control of the processor 26, the valve 34 is closed and the pump 32 activated. Accordingly, during the time interval from t₁ to t₂, the pressure in the cuff 30 rises to a pressure P_(H), a pressure value chosen to be above the highest expected systolic pressure (e.g. 300 to 330 mm Hg). This pressure value is also stored in memory of the processor 26. During this time interval the brachial arterial blood flow becomes totally interrupted. Effectively, there is no arterial wall flexing or underlying body tissue movement because blood flow is occluded. As explained in connection with FIG. 2C the voltage output from the detector 22 rises to V_(H).

During the time interval from t₁ to t₂, the cuff pressure and detector voltage are sampled and stored at a fixed sampling frequency (chosen in a frequency range from 10 Hertz to ten thousand Hertz). The voltage reading from detector 22 when the pressure in cuff 30 reaches its maximum value P_(H) (at time t₂) is stored in processor 26.

At the time t₂ the pressure in the cuff 20 is released by opening valve 34 under control of the processor 26. During the time interval t₂ to t₃ the voltage output from detector 22 and the pressure in the cuff 30 are sampled and stored at the sampling frequency. During the interval t₂ to t₃ the rate of pressure change within the cuff 30 is about two mm Hg to about six mm Hg per second.

As the cuff pressure is reduced, at some time within the interval t₂ to t₃, the pressure in the cuff 20 is equal to the systolic (highest) arterial blood pressure and the artery snaps open with a sudden flow of blood. In turn, as explained in connection with FIG. 2D, the voltage at the detector 22 experiences a maximum rate of change and falls to a maximum deviation from V_(N), to a voltage value V_(L). This voltage V_(L), detected at t₃, corresponds to the sudden rush of arterial blood filing the formerly occluded artery with a sharp flexing of the artery walls. This sharp flexing of the walls in turn stimulates movement of the tissue overlying the artery and underlying the fabric 16. This movement corresponds to a maximum amplitude for the motion of the tissue underlying the fabric 16. At t₃, corresponding to voltage V_(L), this maximum amplitude in tissue movement forces maximum fabric 16 flexing, sudden elongation, signaling that a peak or systolic pressure P_(s) is present in the brachial artery.

During the interval of time t₃ to t₄ the pressure in the cuff 30 is further decreasing. The voltage and pressure values are sampled at the predetermined frequency. The voltage output at the detector 22 continues to rise during this time interval t₃ to t₄.

When, following the occurrence of the minimum voltage V_(L), the output voltage of the detector again returns to within the predetermined range about the baseline value (within the limits (V_(N)+A and V_(N)−Δ) the pressure in the cuff 20 passes through a point of equivalence with the diastolic (lowest) pressure in the brachial artery, uniquely defining t₄. Any further drop in pressure in the cuff 30, to atmospheric pressure, produces no further rise in voltage at detector 22 during the time interval t₄ to t_(t).

The system and method of the present invention may alternatively be operated in a transmission mode where the source 18 is disposed on side 16E of the fabric 16 while the detector 22 is disposed on the opposite side 161. Such a disposition of source 18 and detector 22 is indicated in FIGS. 2A through 2D, where detector 22, on side 161, is indicated in dot-dashed outline. The light balance between reflection and transmission will be the same as the situation discussed in connection with the reflection mode. However, the detector output voltage shown in FIG. 2F is reversed since more fabric stretch results in higher light transmission providing a commensurately higher detector voltage. The detector voltage waveform shown in FIG. 3 is therefore reversed in its sense. In FIG. 3, between the interval of time t₁ to t₂ the voltage is going low and reverses to high going between the interval of time t₂ to t₃. Finally, in FIG. 3 the detector voltage between t₃ and t₄ returns from high to V_(N).

The measurement of pressures P_(s) and P_(D) is, in principle, determined by means of signal processing techniques known in the art. The skilled person having the benefit of the foregoing disclosure will be further enabled by using a commercially available pressure transducer 36, from Advanced Custom Sensors, Inc. Irvine, Calif., 92618; Model 7277 a miniature silicon pressure sensor package, with 0 to 5 volt output; and 0 to 7 pound per square inch gage rating. This pressure transducer 36 will communicate directly with signal processor 26; for example, a Z8® microcontroller, Model Z86C08 from ZILOG, Inc., Campbell, Calif., 95008-6600 with electronically programmable memory and associated circuitry.

Those skilled in the art, having the benefit of the teachings of the present invention as hereinabove set forth, may effect modifications thereto. Such modifications are to be construed as lying within the scope of the present invention, as defined by the appended claims. 

1. A system for monitoring at least one predetermined physiological parameter of a wearer, comprising: a monitoring fabric having a first side defining an exterior surface and having a second side defining an interior surface in contact with or closer to the wearer than the exterior surface when the monitoring system is worn by the wearer, wherein the monitoring fabric comprises a first plurality of reflective yarns knitted or woven with a second plurality of stretchable yarns, said fabric having a region thereof defining gaps of a first size between yarns when said fabric is stretched and defining gaps of a second size between yarns that is different from said first size when the fabric recovers from stretch; at least one source of radiation having wavelength(s) in the range from about 400 to about 2200 nanometers positioned external to the fabric to direct radiation onto the exterior surface and onto the region; at least one detector responsive to incident radiation having wavelength(s) in the range from about 400 to about 2200 nanometers, to produce a signal representative thereof, with said detector mounted to either the first side or the second side of the fabric and external to the fabric, wherein the source and detector are associated with the fabric in fixed or substantially fixed relative positions with respect to the region such that the reception of incident radiation by the detector at a first time interval when the fabric is stretched as compared to the reception of incident radiation by the detector at a second time interval when the fabric recovers from stretch is directly affected by a change in the amount of light reflected by yarns or transmitted through the gaps as the fabric of the region periodically stretches and recovers from stretch in response to at least one predetermined physiological parameter of the wearer; and a signal processor that converts periodically varying signal output received from the detector or from a data acquisition unit associated with the detector into a signal representative of the at least one predetermined physiological parameter of the wearer of the monitoring fabric.
 2. The monitoring system of claim 1 wherein the signal processor converts the signal representative of radiation with a wavelength in the range from about 400 to about 2200 nanometers incident on the detector into a signal representative of at least a predetermined physiological parameter of the wearer of the garment.
 3. The monitoring system of claim 1 wherein each reflective yarn has a coating of an electrically conductive material thereon.
 4. The monitoring system of claim 1 wherein each stretchable yarn is formed as a combination of a covered elastic yarn and a hard yarn.
 5. The monitoring system of claim 1 wherein the source and the detector are mounted on opposing sides of the fabric.
 6. The monitoring system of claim 1 wherein the source and the detector are mounted on a same side of the fabric.
 7. The monitoring system of claim 1 wherein the signal processor is mounted in the monitoring fabric, and wherein the monitoring fabric further comprises: a conductive pathway disposed on or in the fabric connecting the detector and the signal processor.
 8. The monitoring system of claim 1, wherein the monitoring fabric is formed as a patch disposed in or on a sleeve or other wearer-contacting garment.
 9. The monitoring system of claim 8, wherein the patch is sewn, glued, taped, buttoned, interwoven or attached to the sleeve or other wearer-contacting garment.
 10. The monitoring system of claim 1, wherein the at least one predetermined physiological parameter is blood pressure.
 11. A sleeve or encircling garment for monitoring at least one predetermined physiological parameter of a wearer, comprising: a monitoring fabric having a first side defining an exterior surface and having a second side defining an interior surface in contact with or closer to the wearer than the exterior surface when the sleeve is worn by the wearer, wherein the monitoring fabric comprises a first plurality of reflective yarns knitted or woven with a second plurality of stretchable yarns, said fabric having a region thereof defining gaps of a first size between yarns when said fabric is stretched and defining gaps of a second size between yarns that is different from said first size when the fabric recovers from stretch; at least one source of radiation having wavelength(s) in the range from about 400 to about 2200 nanometers positioned external to the fabric to direct radiation onto the exterior surface and onto the region; and at least one detector responsive to incident radiation having wavelength(s) in the range from about 400 to about 2200 nanometers, to produce a signal representative thereof, with said detector mounted to either the first side or the second side of the fabric and external to the fabric.
 12. The sleeve or garment of claim 11, wherein each reflective yarn has a coating of a specularly reflective material thereon.
 13. The sleeve or garment of claim 11, wherein the source and the detector are mounted on opposing sides of the fabric.
 14. The sleeve or garment of claim 11, wherein the monitoring fabric is formed as a patch disposed in or on the sleeve or garment.
 15. The sleeve or garment of claim 14, wherein the source and detector are mounted on the same side of the patch.
 16. The sleeve or garment of claim 14, wherein the patch is sewn, glued, taped, buttoned, interwoven or attached to the sleeve or other garment.
 17. The sleeve or garment of claim 11, wherein the at least one predetermined physiological parameter is blood pressure. 